US3852598A - Scintillation camera with improved resolution - Google Patents

Scintillation camera with improved resolution Download PDF

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Publication number
US3852598A
US3852598A US00308539A US30853972A US3852598A US 3852598 A US3852598 A US 3852598A US 00308539 A US00308539 A US 00308539A US 30853972 A US30853972 A US 30853972A US 3852598 A US3852598 A US 3852598A
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collimator
detector
radiation
demodulation
combination
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A Larsson
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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
    • G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
    • G01T1/16—Measuring radiation intensity
    • G01T1/161—Applications in the field of nuclear medicine, e.g. in vivo counting
    • G01T1/164—Scintigraphy
    • G01T1/1641—Static instruments for imaging the distribution of radioactivity in one or two dimensions using one or several scintillating elements; Radio-isotope cameras
    • G01T1/1642—Static instruments for imaging the distribution of radioactivity in one or two dimensions using one or several scintillating elements; Radio-isotope cameras using a scintillation crystal and position sensing photodetector arrays, e.g. ANGER cameras

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  • the present invention deals with a camera-type system for the detection, registration and documentation of ionizing radiation, hereinafter called radiation quanta.
  • These camera-type systems can have various designs with the main variationsbeing in the type of detector or transducer which is utilized.
  • the most commonly employed transducer is a scintillation crystal and thus the camera-type system will hereinafter be referred to as a scintillation camera.
  • a scintillation camera system useful for this invention will also be provided with a multichannel collimator.
  • Multichannel collimators are constructed of a material with a high absorption for the radiation quanta to be detected and contain a number of parallel, diverging, or converging channels which the radiation quanta traverse to reach the detecting transducer without being absorbed.
  • Scintillation cameras are used primarily in medicine when the distribution of radionuclides in a human organ is to be mapped. In this application, it is attempted to make the radionuclide mapping as detailed as possible.
  • the sharpness in detail in mapping the radionuclide distribution in or around the organ is determined by the resolution of the collimator, through which travel only those radiation quanta which are incident within a limited solid angle on a limited part of the detector transducer, together with the combined resolution of the detector, display, recording, and documentation system.
  • the collimator resolution i.e. its capability to distinguish, for example, two separated point sources of radiation
  • its sensitivity i.e. the degree to which incident radiation quanta reach the detector
  • the collimator can be dimensioned to have good resolution at low sensitivity or vice versa.
  • a collimator's resolution is dependent upon the size of the cross section of the channel which the radiation quanta traverse in reaching the detector.
  • the collimator resolution is also dependent upon the length of the collimator channel as well as the distance between the exit face of the collimator and detector and between the entrance face of the collimator and the radiation source.
  • a quantum of radiation traversing a collimator channel has a particular probability of interacting with the detecting transducer.
  • the energy of the radiation quantum is converted into a different form of energy which produces an output signal in the recording system which carries information concerning the coordinate location of the interaction in the transducer.
  • the signal carrying position information possibly after amplification, data processing and data storage, produces an image on a display device, for example, a brief lightspot on a cathode ray tube, showing where the radiation quanta interacted with the transducer.
  • Image information in a display device can be subjected to data processing before display and documentation or can be documented directly from a dis play device to a documentation device such as photographic film.
  • the detector itself can comprise several devices, in accordance with this invention, which together constitute the detector, recording and display system.
  • the collimator resolution is to be ideal, i.e. such that two very small radiation sources located in front of the collimators and very close to each other will be imaged in a resolved manner in the documentation system (on the assumption that the other parts of the system have ideal resolution) the cross section of the channel would, among other things, have to be very small while its length would have to be very great.
  • the radiation quanta which are emitted from a radioactive point source located in front of the collimator and interacting in the detecting transducer have only a single path through the collimator channels if the collimator has ideal resolution.
  • the radiation quanta interacting in the detector therefore carry information that they originate from a radiation source located on a straight line from an interaction point in the detector and travelling coaxially through the collimator channel, i.e. the channel traversed by the radiation quanta in reaching the point of interaction. This can also be expressed in terms that the radiationquanta from a particular point source can reach an interaction point in the detector only through one collimator channel.
  • the size of the cross section of collimator channels cannot be very small, i.e. less than 1mm, and the length of the channels cannot be very great, i.e. greater than 20 cm.
  • a larger cross section produces the result that the radiation quanta emitted from a radioactive point-source located in front of the collimator and interacting in the detector do not necessarily have to pass only through one channel in the collimator. This has the result that the collimator resolution deteriorates, i.e. it is not ideal.
  • This invention is characterized in that the imagedeteriorating effect produced by the non-ideality of the collimator resolution is partly eliminated without significantly reducing the collimator sensitivity.
  • This is achieved by employing an optical or electronic correction device, hereinafter called a demodulator.
  • This demodulator if it is an optical one, can be placed between the detectors display system and a documentation system.
  • An optical demodulator can also be placed between the completed document, for example, photographic tilm, and a redisplay or redocumentation system, and thus does not need to be an integral unit of the scintillation camera.
  • the demodulator is electronic, it can be placed into the registration system and there can be considered to process the detector output signals carrying position information before they are fed to the display system.
  • the demodulator can be considered to consist of a number of demodulator elements, one element for each collimator channel, where each element produces the mirror-image of the information-carrying signal from a corresponding collimator channel before documentation or redisplay.
  • Each element has a position corresponding to that of its associated collimator channel, and in an application in which the collimator is moved, the demodulator is given a synchronized movement with the collimator.
  • the demodulator can be. constructed such that a particular degree of improvement of the resolving power of the overall system is obtained.
  • the mirror-imaging elements of the demodulator can consist of a channel in an opaque disk. This channel therefore functions like a camera pinhole.
  • a lens or lens system can produce the same result as the abovecited channel.
  • each element in the demodulator forms a mir ror-image of information-carrying signals from each associated collimator channel, the resultant signal will be documented closer to the location it would have been documented if the collimator resolution were ideal, i.e. the image-deteriorating effect which is produced by the fact that the radiation quanta emitted from one and the same point-shaped radioactive source reach the detector through more than one channel is partially eliminated.
  • FIG. 1 is a schematic representation of portions of a scintillation camera in cross section together with graphical representations of system response;
  • FIG. 2 is a schematic representation in cross section of portions of a scintillation camera and a generalizedsystem employing an optical demodulator in accordance with this invention.
  • FIG.- 7 is a block diagram of a scintillation camera system employing an electronic demodulator in accordance with this invention.
  • FIG. 1 shows schematically in cross section the relationships between a multichannel collimator a, detector b, registration system cand documentation system d, and the detected intensity B in detector B, recorded intensity C in the registration system c and the documented intensity D in the documentation system d in the detection, registration, and documentation of radioactive radiation from a point-shaped radioactive source p with, for example, a scintillation camera.
  • the quanta of radiation which are emitted from source p can travel to the detector b only through channels a3, a4 and a5 in multichannel collimator a.
  • the quanta which are emitted from source p toward point b4 in the detector b are absorbed in wall 012 between channel 01 and channel a2 and thus will not be detected.
  • the quanta from source p which pass through channel a3 in collimator a are detected between points b3 and b2 in detector b and the detected intensity B thus is increased in the region between points 03 and c2 in the registration system c and at the same time, the documented intensity D is increased between points d3 and d2 in the documentation system d.
  • the registration system c and documentation system d a conical image of the quanta detected in detector b is formed.
  • detector b has ideal resolution. If the collimator resolution were ideal only the quanta which are emitted from source p to point bl in detector b would be detected and thus registered at point 01 of the registration differ in time.
  • each other and operatively associated with certain zones bcl, bc2, bc3,' bc4, bcS, 1206 and bcn in detector be and zones fl,f 2, f3, f4, j5,fl$ and fn on screen f.
  • Each zone bcI-bcn in detector be is operatively associated with the respective channels aI-an in collimator a. Only the quanta which, for example, are transmitted through channel cm, are detected in zone bcn and displayed or documented in zone fn.
  • Each unit gl-gn has a mirror-imaging effect on the signals from the detected quanta in the respective zone bcI-bcn.
  • the principle consists of the fact that the quanta incident on point bclO along line s1 in detector be interact there and'give rise to a signal carrying position information which passes through element g] in demodulator 3, after which documentation occurs at point fll of screen f and not at point fit) as would have been the case if no demodulator had been there.
  • the quanta which are emitted from the radioactive point source p to detector be are displayed or documented in zone p2 when they have passed demodulator g and in zone pl if no demodulator is present. Since zone p2 is smaller in its extension than zone p1, the resolution is increased with the use of demodulator g.
  • FIG. 3 shows a cross section of a version of the invention where the mirror-imaging demodulation units consist of so-called pin-holes ghl-ghn in demodulator gh.
  • Each pin-hole ghl-ghn corresponds to its collimator channel al-an and is located at imaginary axes which pass coaxially through said channels al-an.
  • pinholes ghl-ghn are placed and dimensioned such that no signals carrying position information from the region in the display system c, exemplified by 012, corresponding to the wall or septum regions in collimator a, exemplified by n12, are capable of penetrating to screen d which can serve as a documentation system.
  • the diagram in FIG. 3 shows the detected intensity B from a radioactive point source p, the displayed intensity C as well as the documented intensity 1) of the same said source p.
  • a movement can be imparted to the collimator, as shown by arrow ar, which is synchronized with a movement of demodulator gh, as shown by arrow ghr, in such a manner that each zone under collimator a is mapped.
  • the distribution of the documented intensities DR in principle becomes as indicated by the diagram at the top of FIG. 3.
  • FIG. 4 shows a cross section of a version of the invention which differs from the above-cited version only insofar as the demodulator g1 consists of a number of lenses or lens systems gil-gin which have the same function as pin-holes ghl-ghn in FIG. 3.
  • the signals carrying position information are stored in some data memory where the signals carrying position information from a given zone in the detector are stored in a data memory corresponding to said zone, a so-called measuring cell.
  • the detected and displayed intensity BC of the radioactive point source p will be stored in data memory gk.
  • a certain integral numberof measuring cells in zone gkn, hereinafter called cell group, in data memory gk is assigned to each zone bcn in detector be on which quanta of radiation are incident through collimator channel an associated with zone bcn.
  • measuring cell gknl in the data memory gk corresponds to zone bcnl in detector be, gkn2 to bcn2, etc.
  • the part in the detector which corresponds in cross section to a wall with thickness t between two collimator channels bay in collimator a can be allowed to have such a space in the data memory gk which in cross section corresponds to one or a certain number of measuring cells.
  • the measuring cells put certain information into a matrix with rows xl-xn and columns yl-yn. For example, measuring cell gknl is assigned position x24/y24 in said matrix.
  • the mirror-imaging process is performed such that the content in each measuring cell, except for a possibly centrally located measuring cell in the group, e.g. gknS, is exchanged for the information content in a diametrically opposite measuring cell according to the diagram shown in FIG. 5. Consequently, the information stored in gknl, i.e. the number of signals carrying position information, will be presented as x26/y26.
  • a multichannel collimator intended to be utilized with this invention can be designed such that it offers an improved resolution in the detection of lower pho- 6 ton energies with unmodified sensitivity.
  • the number of collimators in one and the same scintillation camera can therefore be reduced.
  • this invention is based upon the recognition that radiation quanta from a point source underneath a particular main collimator channel will uniformly illuminate a small zone of the detecting transducer associated with that collimator channel but will only illuminate a portion of a small zone of the detecting transducer associated with the adjacent channels.
  • the portions illuminated through adjacent collimater channels are the ones most remote from the position of the point source so that, if a mirror-image reversal around the axis of each collimator channel is performed, the output signal documented is closer to the position of origin of the quantum of radiation which produced by it.
  • the image from the main collimator channel is reversed but since the illumination is uniform, there is no alteration of that image information.
  • FIG. 6 shows a block diagram of a scintillation camera system employing an optical demodulator version of this invention.
  • Radiation quanta from object 10 traverse collimator (denoted a in FIGS. 1-5) and interact with a radiation sensitive transducer 31 (denoted b in FIGS. 11-4) in detector head 30.
  • Detector head 30 and detector electronics 40 together produce output electrical signals containing position coordinate information which is fed to CRT 50 such that the spatial position of an interaction in transducer 31 is imaged as a correspondingly positioned flash of light on CRT screen 51 (denoted c in FIGS. 1-4).
  • optical demodulator 60 which may be the array of pinhole demodulating ele- 'ments ghl-ghn of FIG. 3 or the lens elements gil-gin of FIG. 4, and are documented on a documentation medium such as film 71 (denoted d in FIGS. 1-4) in camera 70.
  • a synchronous scanning apparatus produces synchronous scanning of collimator 20 and demodulator 60.
  • FIG. 7 shows a block diagram of a scintillation camera system employing an electronic demodulation version of this invention.
  • position coordinate output signals from detector electronics are stored in data storage'and computer apparatus in which the stored image information is processed digitally to produce the required mirror image reversal around the position of the axis of each collimator channel.
  • the mirror image reversal is performed before display on screen 151 of CRT 150 and documentation on film 171 in camera and scanning apparatus produces scanning of collimator 120 and provides collimator position signals to data storage and computer apparatus 160.
  • a radiation detector including a radiation sensitive transducer, of the type producing an output representing spatial coordinates of interaction of a quantum of radiation with said transducer;
  • a collimator mounted on said detector adjacent said demodulation means receiving said output of said detector operative to produce on said documentation medium a documenting spot at a position comprising a mirror image reversal of said spatial coordinates of interaction with respect to a central axis of one of said channels traversed by said quantum of radiation.
  • said radiation detector further includes a CRT display means and said output comprises a spatially located flash of light on said CRT display means; said documentation means comprises a sheet of photographic film; and said demodulation means comprises optical demodulation means mounted between said CRT display means and said photographic film and having an array of demodulation elements corresponding to said 6.
  • said output of said radiation detector comprises a pair of coordinate electrical signals; and said demodulation means comprises data storage and computing means receiving said coordinate electrical signals operative to translate said'signals into demodulated electrical signals and display means for displaying said demodulated electrical signals.

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  • Physics & Mathematics (AREA)
  • Health & Medical Sciences (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Biomedical Technology (AREA)
  • General Health & Medical Sciences (AREA)
  • Medical Informatics (AREA)
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  • Life Sciences & Earth Sciences (AREA)
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US00308539A 1971-11-23 1972-11-21 Scintillation camera with improved resolution Expired - Lifetime US3852598A (en)

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SE14953/71A SE361948B (no) 1971-11-23 1971-11-23

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CA (1) CA963181A (no)
DE (1) DE2257493A1 (no)
FR (1) FR2163037A5 (no)
GB (1) GB1387895A (no)
NL (1) NL7215879A (no)
SE (1) SE361948B (no)

Cited By (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4212061A (en) * 1977-12-21 1980-07-08 Medtronic, Inc. Radiation signal processing system
US4281382A (en) * 1977-12-21 1981-07-28 Medtronic, Inc. Radiation signal processing system
US4386404A (en) * 1979-12-03 1983-05-31 Medtronic, Inc. Radiation signal processing system
US4817038A (en) * 1977-12-21 1989-03-28 Siemens Gammasonics, Inc. Radiation signal processing system
US5429135A (en) * 1992-03-10 1995-07-04 Siemens Medical Systems, Inc. Determining the depth of an organ which is the subject of a nuclear medicine study using only planar image data
US5500886A (en) * 1994-04-06 1996-03-19 Thermospectra X-ray position measuring and calibration device
US11058892B2 (en) 2017-05-05 2021-07-13 Zap Surgical Systems, Inc. Revolving radiation collimator
US11844637B2 (en) 2017-09-06 2023-12-19 Zap Surgical Systems, Inc. Therapeutic radiation beam detector for radiation treatment systems

Families Citing this family (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPS6034018A (ja) * 1983-08-06 1985-02-21 Canon Inc Ｘ線コリメ−タと露光装置
EP3627994B1 (en) * 2017-05-05 2024-08-21 Zap Surgical Systems, Inc. Revolving radiation collimator

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3320418A (en) * 1964-06-01 1967-05-16 Ohio Nuclear Scanning means including a screen which blocks radiation according to the probability of its origin
US3418471A (en) * 1963-11-07 1968-12-24 Richard W Hanes Visualizing internal structure
US3631244A (en) * 1969-03-13 1971-12-28 Nuclear Chicago Corp Tomographic radiation camera with mechanical readout

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3418471A (en) * 1963-11-07 1968-12-24 Richard W Hanes Visualizing internal structure
US3320418A (en) * 1964-06-01 1967-05-16 Ohio Nuclear Scanning means including a screen which blocks radiation according to the probability of its origin
US3631244A (en) * 1969-03-13 1971-12-28 Nuclear Chicago Corp Tomographic radiation camera with mechanical readout

Cited By (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4212061A (en) * 1977-12-21 1980-07-08 Medtronic, Inc. Radiation signal processing system
US4281382A (en) * 1977-12-21 1981-07-28 Medtronic, Inc. Radiation signal processing system
US4817038A (en) * 1977-12-21 1989-03-28 Siemens Gammasonics, Inc. Radiation signal processing system
US4386404A (en) * 1979-12-03 1983-05-31 Medtronic, Inc. Radiation signal processing system
US5429135A (en) * 1992-03-10 1995-07-04 Siemens Medical Systems, Inc. Determining the depth of an organ which is the subject of a nuclear medicine study using only planar image data
US5500886A (en) * 1994-04-06 1996-03-19 Thermospectra X-ray position measuring and calibration device
US11058892B2 (en) 2017-05-05 2021-07-13 Zap Surgical Systems, Inc. Revolving radiation collimator
US11826582B2 (en) 2017-05-05 2023-11-28 Zap Surgical Systems, Inc. Revolving radiation collimator
US11844637B2 (en) 2017-09-06 2023-12-19 Zap Surgical Systems, Inc. Therapeutic radiation beam detector for radiation treatment systems

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DE2257493A1 (de) 1973-05-30
SE361948B (no) 1973-11-19
GB1387895A (en) 1975-03-19
FR2163037A5 (no) 1973-07-20
CA963181A (en) 1975-02-18
NL7215879A (no) 1973-05-25

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